Gentle to skin adhesive

ABSTRACT

Electron beam and gamma radiation crosslinked, silicone gel adhesives are described. Both nonfunctional and functional poly diorganosiloxanes are used. Methods of forming the adhesives, and medical articles incorporating such adhesives are also described.

This application claims the benefit of U.S. Provisional Application No.61/109,211 (filed Oct. 29, 2008), and U.S. Provisional Application No.61/109,213 (filed Oct. 29, 2008); both of which are herein incorporatedby reference in their entireties.

FIELD

The present disclosure relates to gentle to skin adhesives.Specifically, to silicone gel adhesives and methods of making suchadhesives. Such methods include electron beam or gamma ray curing of lowmolecular weight silicones, including non-functional silicones.

SUMMARY

Briefly, in one aspect, the present disclosure provides an adhesivecomprising a radiation cured silicone gel. The silicone gel comprises acrosslinked poly diorganosiloxane material.

In another aspect, the present disclosure provides an adhesive formed byexposing a composition comprising a poly diorganosiloxane material to atleast one of electron beam irradiation and gamma irradiation at asufficient dose to crosslink the poly diorganosiloxane material.

In some embodiments, the poly diorganosiloxane material comprises a polydimethylsiloxane. In some embodiments, the poly dimethylsiloxane isselected from the group consisting of one or more silanol terminatedpoly dimethylsiloxanes, one or more non-functional polydimethylsiloxanes, and combinations thereof. In some embodiments, thepoly dimethylsiloxane consists of one or more non-functional polydimethylsiloxanes.

In some embodiments, the adhesive further comprises a silicate resintackifier. In some embodiments, the adhesive further comprises apoly(dimethylsiloxane-oxamide) linear copolymer.

In some embodiments, the poly diorganosiloxane material comprises a polydiorganosiloxane fluid having a dynamic viscosity at 25° C. of nogreater than 1,000,000 mPa·sec. In some embodiments, the polydiorganosiloxane material consists of poly diorganosiloxane fluidshaving a kinematic viscosity at 25° C. of no greater than 100,000centistokes.

In some embodiments, the adhesive has a 180 degree peel adhesion fromhuman skin of no greater than 200 grams per 2.54 centimeters as measuredaccording to the Skin Peel Adhesion Procedure.

In yet another aspect, the present disclosure provides a medical articlecomprising a layer of any of the silicone adhesives of the presentdisclosure adhered to a medical substrate. In some embodiments, thelayer has a thickness of 20 to 200 microns. In some embodiments, themedical substrate comprises at least one of paper, polymeric film, andwoven cloth and non-woven cloth,

In a further aspect, the present disclosure provides a method ofadhering a medical substrate to a biological substrate. The methodcomprises adhering an adhesive according to the present disclosure tothe medical substrate, and using the adhesive to adhere the medicalsubstrate to the biological substrate. In some embodiments, thebiological substrate is human skin.

The above summary of the present disclosure is not intended to describeeach embodiment of the present invention. The details of one or moreembodiments of the invention are also set forth in the descriptionbelow. Other features, objects, and advantages of the invention will beapparent from the description and from the claims.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 illustrates a medical article according to some embodiments ofthe present disclosure.

DETAILED DESCRIPTION

The application of pressure sensitive adhesives (PSAs), includingsilicone pressure sensitive adhesives, for adhering to skin is known inthe art and many examples are commercially available. However, someproperties of PSAs limit their application for adhesion to skin. Forinstance, skin damage may result during the removal of a PSA thatexhibits too high a level of adhesive strength. Alternatively, if theadhesive strength is reduced, the PSA may lack sufficient holding powerto be useful or will lose the room temperature tackiness that makes easyapplication of the adhesive possible. Additionally PSAs that arerelatively rigid or non-conformable compared to skin typically result inconsiderable patient discomfort during use. Also, even adhesives thathave a measured low peel adhesion to skin may cause discomfort duringremoval, e.g., if the adhesive becomes entangled with hair

Silicone gel (crosslinked poly dimethylsiloxane (“PDMS”) materials havebeen used for dielectric fillers, vibration dampers, and medicaltherapies for promoting scar tissue healing. Lightly crosslinkedsilicone gels are soft, tacky, elastic materials that have low tomoderate adhesive strength compared to traditional, tackified siliconePSAs. Silicone gels are typically softer than silicone PSAs, resultingin less discomfort when adhered to skin. The combination of relativelylow adhesive strength and moderate tack make silicone gels suitable forgentle to skin adhesive applications.

Silicone gel adhesives provide good adhesion to skin with gentle removalforce and have the ability to be repositioned. Examples of commerciallyavailable silicone gel adhesive systems include products marketed withthe trade names: Dow Corning MG 7-9850, WACKER 2130, BLUESTAR 4317 and4320, and NUSIL 6345 and 6350.

These gentle skin adhesives are formed by an addition cure reactionbetween vinyl-terminated poly(dimethylsiloxane) (PDMS) and hydrogenterminated PDMS, in the presence of a hydrosilation catalyst (e.g.,platinum complex). Vinyl-terminated and hydrogen terminated PDMS chainsare referred to as ‘functionalized’ silicones due to their specificchemical moieties. Individually, such functional silicones are generallynot reactive; however, together they form a reactive silicone system.Additionally, silicate resins (tackifiers) and PDMS with multiplehydrogen functionalities (crosslinkers) can be formulated to modify theadhesive properties of the gel.

The silicone gel adhesives resulting from the addition cure reaction arevery lightly crosslinked polydimethysiloxane (PDMS) networks with somelevel of free (not crosslinked) PDMS fluid and little or no tackifiyingresin. By contrast, tackifying resins are typically used at high levels(45-60 pph) in silicone PSAs.

In addition to the catalyst-promoted curing of silicone materials, it isknown that free radicals formed from the high temperature degradation oforganic peroxides can crosslink or cure silicone PSA formulations. Thiscuring technique is undesirable due to the acidic residues left in thefilm from the curing chemistry, which are corrosive and unsuitable forskin contact.

Generally, the crosslinked siloxane networks of the present disclosurecan be formed from either functional or non-functional siliconematerials. These gel adhesives have excellent wetting characteristics,due to the very low glass transition temperature (Tg) and modulus of thepolysiloxane network. Rheologically, these gels exhibit nearly identicalstorage moduli at bond making and bond breaking time scales, resultingin relatively low to moderate forces being required to debond theadhesive by peeling. This results in minimal to no skin trauma uponremoval. Additionally, the elastic nature of the crosslinked gelprevents flow of the adhesive around hair during skin wear, furtherreducing the instances of pain during removal.

Generally, the silicone materials may be oils, fluids, gums, elastomers,or resins, e.g., friable solid resins. Generally, lower molecularweight, lower viscosity materials are referred to as fluids or oils,while higher molecular weight, higher viscosity materials are referredto as gums; however, there is no sharp distinction between these terms.Elastomers and resins have even higher molecular weights that gums, andtypically do not flow. As used herein, the terms “fluid” and “oil” referto materials having a dynamic viscosity at 25° C. of no greater than1,000,000 mPa·sec (e.g., less than 600,000 mPa·sec), while materialshaving a dynamic viscosity at 25° C. of greater than 1,000,000 mPa·sec(e.g., at least 10,000,000 mPa·sec) are referred to as “gums”.

Generally, the silicone materials useful in the present disclosure arepoly diorganosiloxanes, i.e., materials comprising a polysiloxanebackbone. In some embodiments, the nonfunctionalized silicone materialscan be a linear material described by the following formula illustratinga siloxane backbone with aliphatic and/or aromatic substituents:

wherein R1, R2, R3, and R4 are independently selected from the groupconsisting of an alkyl group and an aryl group, each R5 is an alkylgroup and n and m are integers, and at least one of m or n is not zero.In some embodiments, one or more of the alkyl or aryl groups may containa halogen substituent, e.g., fluorine. For example, in some embodiments,one or more of the alkyl groups may be —CH₂CH₂C₄F₉.

In some embodiments, R5 is a methyl group, i.e., the nonfunctionalizedpoly diorganosiloxane material is terminated by trimethylsiloxy groups.In some embodiments, R1 and R2 are alkyl groups and n is zero, i.e., thematerial is a poly(dialkylsiloxane). In some embodiments, the alkylgroup is a methyl group, i.e., poly(dimethylsiloxane) (“PDMS”). In someembodiments, R1 is an alkyl group, R2 is an aryl group, and n is zero,i.e., the material is a poly(alkylarylsiloxane). In some embodiments, R1is methyl group and R2 is a phenyl group, i.e., the material ispoly(methylphenylsiloxane). In some embodiments, R1 and R2 are alkylgroups and R3 and R4 are aryl groups, i.e., the material is apoly(dialkyldiarylsiloxane). In some embodiments, R1 and R2 are methylgroups, and R3 and R4 are phenyl groups, i.e., the material ispoly(dimethyldiphenylsiloxane).

In some embodiments, the nonfunctionalized poly diorganosiloxanematerials may be branched. For example, one or more of the R1, R2, R3,and/or R4 groups may be a linear or branched siloxane with alkyl or aryl(including halogenated alkyl or aryl) substituents and terminal R5groups.

As used herein, “nonfunctional groups” are either alkyl or aryl groupsconsisting of carbon, hydrogen, and in some embodiments, halogen (e.g.,fluorine) atoms. As used herein, a “nonfunctionalized polydiorganosiloxane material” is one in which the R1, R2, R3, R4, and R5groups are nonfunctional groups.

Generally, functional silicone systems include specific reactive groupsattached to the polysiloxane backbone of the starting material (forexample, hydrogen, hydroxyl, vinyl, allyl, or acrylic groups). As usedherein, a “functionalized poly diorganosiloxane material” is one inwhich at least one of the R-groups of Formula 2 is a functional group.

In some embodiments, a functional poly diorganosiloxane material is oneis which at least 2 of the R-groups are functional groups. Generally,the R-groups of Formula 2 may be independently selected. In someembodiments, at least one functional group is selected from the groupconsisting of a hydride group, a hydroxy group, an alkoxy group, a vinylgroup, an epoxy group, and an acrylate group.

In addition to functional R-groups, the R-groups may be nonfunctionalgroups, e.g., alkyl or aryl groups, including halogenated (e.g.,fluorinated) alky and aryl groups. In some embodiments, thefunctionalized poly diorganosiloxane materials may be branched. Forexample, one or more of the R groups may be a linear or branchedsiloxane with functional and/or non-functional substituents.

The gentle to skin adhesives of the present disclosure may be preparedby combining one or more poly diorganosiloxane materials (e.g., siliconeoils or fluids), optionally with an appropriate tackifying resin,coating the resulting combination, and curing using electron beam(E-beam) or gamma irradiation. Generally, any known additives useful inthe formulation of adhesives may also be included.

If included, generally, any known tackifying resin may be used, e.g., insome embodiments, silicate tackifying resins may be used. In someexemplary adhesive compositions, a plurality of silicate tackifyingresins can be used to achieve desired performance.

Suitable silicate tackifying resins include those resins composed of thefollowing structural units M (i.e., monovalent R′₃SiO_(1/2) units), D(i.e., divalent R′₂SiO_(2/2) units), T (i.e., trivalent R′SiO_(3/2)units), and Q (i.e., quaternary SiO_(4/2) units), and combinationsthereof. Typical exemplary silicate resins include MQ silicatetackifying resins, MQD silicate tackifying resins, and MQT silicatetackifying resins. These silicate tackifying resins usually have anumber average molecular weight in the range of 100 to 50,000-gm/mole,e.g., 500 to 15,000 gm/mole and generally R′ groups are methyl groups.

MQ silicate tackifying resins are copolymeric resins where each M unitis bonded to a Q unit, and each Q unit is bonded to at least one other Qunit. Some of the Q units are bonded to only other Q units. However,some Q units are bonded to hydroxyl radicals resulting in HOSiO_(3/2)units (i.e., “T^(OH)” units), thereby accounting for some silicon-bondedhydroxyl content of the silicate tackifying resin.

The level of silicon bonded hydroxyl groups (i.e., silanol) on the MQresin may be reduced to no greater than 1.5 weight percent, no greaterthan 1.2 weight percent, no greater than 1.0 weight percent, or nogreater than 0.8 weight percent based on the weight of the silicatetackifying resin. This may be accomplished, for example, by reactinghexamethyldisilazane with the silicate tackifying resin. Such a reactionmay be catalyzed, for example, with trifluoroacetic acid. Alternatively,trimethylchlorosilane or trimethylsilylacetamide may be reacted with thesilicate tackifying resin, a catalyst not being necessary in this case.

MQD silicone tackifying resins are terpolymers having M, Q and D units.In some embodiments, some of the methyl R′ groups of the D units can bereplaced with vinyl (CH2=CH—) groups (“D^(Vi)” units). MQT silicatetackifying resins are terpolymers having M, Q and T units.

Suitable silicate tackifying resins are commercially available fromsources such as Dow Corning (e.g., DC 2-7066), Momentive PerformanceMaterials (e.g., SR545 and SR1000), and Wacker Chemie AG (e.g., BELSILTMS-803).

The polsiloxane material, the tackifying resin, if present, and anyoptional additives may be combined by any of a wide variety of knownmeans prior to being coated and cured. For example, in some embodiments,the various components may be pre-blended using common equipment such asmixers, blenders, mills, extruders, and the like.

In some embodiments, the materials may be dissolved in a solvent,coated, and dried prior to curing. In some embodiments, solventlesscompounding and coating processes may be used. In some embodiments,solventless coating may occur at about room temperature. For example, insome embodiments, the materials may have kinematic viscosity of nogreater than 100,000 centistokes (cSt), e.g., no greater than 50,000cSt. However, in some embodiments, hot melt coating processes such asextrusion may be used, e.g., to reduce the viscosity of higher molecularweight materials to values more suitable for coating. The variouscomponents may be added together, in various combinations orindividually, through one or more separate ports of an extruder, blended(e.g., melt mixed) within the extruder, and extruded to form the hotmelt coated composition.

Regardless of how it is formed, the coated compositions are radiationcured. In some embodiments, coating may be cured through exposure toE-beam irradiation. In some embodiments, the coating may be curedthrough exposure to gamma irradiation. In some embodiments, acombination of electron beam curing and gamma ray curing may be used.For example, in some embodiments, the coating may be partially cured byexposure to electron beam irradiation. Subsequently, the coating may befurther cured by gamma irradiation.

A variety of procedures for E-beam and gamma ray curing are well-known.The cure depends on the specific equipment used, and those skilled inthe art can define a dose calibration model for the specific equipment,geometry, and line speed, as well as other well understood processparameters.

Commercially available electron beam generating equipment is readilyavailable. For the examples described herein, the radiation processingwas performed on a Model CB-300 electron beam generating apparatus(available from Energy Sciences, Inc. (Wilmington, Mass.). Generally, asupport film (e.g., polyester terephthalate support film) runs through achamber. In some embodiments, a sample of uncured material with a liner(e.g., a fluorosilicone release liner) on both sides (“closed face”) maybe attached to the support film and conveyed at a fixed speed of about6.1 meters/min (20 feet/min). In some embodiments, a sample of theuncured material may be applied to one liner, with no liner on theopposite surface (“open face”). Generally, the chamber is inerted (e.g.,the oxygen-containing room air is replaced with an inert gas, e.g.,nitrogen) while the samples are e-beam cured, particularly whenopen-face curing.

The uncured material may be exposed to E-beam irradiation from one sidethrough the release liner. For making a single layer laminating adhesivetype tape, a single pass through the electron beam may be sufficient.Thicker samples, may exhibit a cure gradient through the cross sectionof the adhesive so that it may be desirable to expose the uncuredmaterial to electron beam radiation from both sides.

Commercially available gamma irradiation equipment includes equipmentoften used for gamma irradiation sterilization of products for medicalapplications. In some embodiments, such equipment may be used to cure,or partially cure the gentle to skin adhesives of the presentdisclosure. In some embodiments, such curing may occur simultaneouslywith a sterilization process for a semi-finished or finished product,for example a tape or wound dressing.

In some embodiments, the gentle to skin adhesives of the presentdisclosure are suitable for forming medical articles such as tapes,wound dressings, surgical drapes, IV site dressings, a prosthesis, anostomy or stoma pouch, a buccal patch, or a transdermal patch. In someembodiments, the adhesives may also be useful for other medical articlesincluding dentures and hairpieces.

In some embodiments, the adhesives may include any of a variety of knownfillers and additives including, but not limited to, tackifiers (e.g.,MQ resins), fillers pigments, additives for improving adhesion,additives for improving moisture-vapor transmission rate, pharmaceuticalagents, cosmetic agents, natural extracts, silicone waxes, siliconepolyethers, hydrophilic polymers and rheology modifiers. Additives usedto improve adhesion, particularly to wet surfaces, include polymers suchas poly(ethylene oxide) polymers, poly(propylene oxide) polymers andcopolymers of poly(ethylene oxide and propylene oxide), acrylic acidpolymers, hydroxyethyl cellulose polymers, silicone polyethercopolymers, such as copolymers of poly(ethylene oxide) andpolydiorganosiloxane and copolymers of poly(propylene oxide) andpolydiorganosiloxane, and blends thereof.

In some embodiments, the gentle to skin adhesives of the presentdisclosure are suitable for adhering a medical substrate to a biologicalsubstrate (e.g., a human or an animal). For example, in someembodiments, the gentle to skin adhesives of the present disclosure maybe used to adhere medical substrates to the skin of humans and/oranimals.

Exemplary medical substrates include polymeric materials, plastics,natural macromolecular materials (e.g., collagen, wood, cork, andleather), paper, woven cloth and non-woven cloth, metals, glass,ceramics, and composites.

The thickness of the adhesive layer is not particularly limited. In someembodiments, the thickness will be at least 10 microns, and in someembodiments, at least 20 microns. In some embodiments, the thicknesswill be no greater than 400 microns, and in some embodiments, no greaterthan 200 microns.

The peel adhesion to biological substrates such as human skin is knownto be highly variable. Skin type, location on the body, and otherfactors can affect results. Generally, average values of peel adhesionfrom skin are subject to large standard deviations. In some embodiments,the average peel adhesion for human skin may be less than 200 gm/2.54cm, and in some embodiments, less than 100 gm/2.54 cm.

Exemplary medical article 100 is illustrated in FIG. 1. Medical article100 comprises silicone adhesive 130 associated with a first majorsurface of substrate 120. Although not shown, in some embodiments, theopposite surface adhesive 130 may be protected by a release liner. Insome embodiments, medical article 100 may be self wound, and theopposite (exposed) surface of the adhesive will come into contact withthe uncoated major surface of substrate 120.

In use, the surface of the adhesive is applied to the biologicalsubstrate, e.g., human skin, adhering substrate 120 to the biologicalsubstrate.

EXAMPLES

E-Beam Curing Procedure. E-beam curing was performed on a Model CB-300electron beam generating apparatus (available from Energy Sciences, Inc.(Wilmington, Mass.). Generally, a support film (e.g., polyesterterephthalate support film) was run through the inerted chamber of theapparatus. Samples of uncured material were attached to the support filmand conveyed at a fixed speed of about 6.1 meters/min (20 feet/min)through the inerted chamber and exposed to electron beam irradiation.

Gamma Beam Curing Process. The irradiation with gamma rays wasaccomplished using a source strength of 1.5 to 3 million curie (MCi)consisting of a series of hollow stainless steel tubes containingcobolt-60 (Co-60). Generally, mid-way through the dose exposure ofmultiple samples, the samples were retrieved from the irradiationchamber, and their relative positions reversed to provide a more uniformexposure. The samples were conveyed into the irradiation chamber andexposed to gamma rays for periods of time necessary to achieve thedesired dose. Total absorbed doses ranged from 0.2 to 3 Mrad (2 to 30kGy) and dose rates were about 0.3 to 0.5 Mrad/hour (3 to 5 kGy/hour).

Peel Test Procedure. Peel adhesion was measured using an IMass 2000 peeltester. The adhesive sample was slit to a width of 1.3 cm (0.5 in.) andlength of 12.7 cm (5 in.). The resulting tape was then applied to aclean polypropylene panel (obtained from Standard Plaque Inc.(Melvindale, Mich.)) using four total passes of a 2 kg (4.5 lb) hardrubber roller. The sample was aged before testing for 20 minutes at roomtemperature (22° C.) and 50% relative humidity. The panel was thenmounted on the bed of the IMass 2000 Tester and the tape was pulled offat a 180 degree angle at a speed of 30.5 cm/minute (12 in/min). Resultswere measured in grams force per 0.5 inch, and converted to g/2.54 cm.

Tack Test Procedure. Tack was measured using a TA-XT Plus TextureAnalyzer equipped with a 6 mm diameter polypropylene cylinder probe. Theadhesive sample was slit to a width of 1.9 cm (0.75 in.) and length of10.2 cm (4 in.) and laminated to a brass bar with 10 mm diameter holesthrough it to allow for the probe to reach the adhesive face of thetape. Test parameters were: Pretest: 0.5 mm/sec, test speed: 1.0 mm/sec,pretest speed: 10.0 mm/sec, applied force: 100 grams, contact time: 5seconds, trigger force: 1 gram, and withdraw distance: 3 mm.

Skin Peel Adhesion Procedure. Four male and two female subjects wereenrolled into this study. The backs of all subjects were washed usingIVORY SOAP prior to sample application. The adhesive samples were slitto a width of 2.54 cm (1.0 in.) and length of 7.62 cm (3 in.) Sampleswere placed on the subject's back positioned so that the long axis ofeach sample was oriented perpendicular to the volunteer's spine. Theorder of application of sample materials was randomized (i.e. rotationalplacement) on each subject. Sample materials were secured using a 2 kg.(4.5-pound) roller of 3M design. The samples were removed at 180 degreesat a rate of 30.5 cm/minute (12 inches per minute). The peel force wasmeasured with a load cell in units of grams force. An initial set ofadhesive materials were applied and immediately removed (“T-0”). Anadditional set of samples were applied and allowed to dwell for 72 hoursbefore removal (“T-72”).

The materials used in the following examples are summarized in Table 1.

TABLE 1 Summary of materials. Material Description Source TMS-803MQ-tackifying resin Wacker Chemie AG EL Polymer NA PDMS gum (a) WackerChemie AG DC-200-A Dow Corning 200 PDMS Dow Corning, fluid (5000 cSt)Midland, MI DC-200-B Dow Corning 200 PDMS Dow Corning, fluid (12,500cSt) Midland, MI DMS-S42 Silanol functional PDMS Gelest, Inc. fluid(18,000 cSt) OHX-4070 Terminal silanol functional XIAMETER, PDMS fluid(50,000 cSt) Midland, MI SPOx poly(dimethylsiloxane-oxamide) Prepared aslinear copolymer described below (a) No reported kinematic viscosity,but this material was a highly viscous gum.

Preparation of SPOx. A silicone polyoxamide (SPOx) elastomer wasprepared in two steps. In the first step, anα,ω-bis(aminopropyl)polydimethylsiloxane diamine with a molecular weightof 25,000 grams/mole was capped with diethyloxalate to provide aα,ω-oxamido oxalate ester capped precursor. (α is the Greek letteralpha, and ω is the Greek letter omega.) This step was completed byfollowing the general procedure of Preparative Example 1 in U.S. Pat.No. 7,371,464. The diethyloxalate is used in a molar excess to thediamine to provide the α,ω-oxamido oxalate ester capped precursor. Thisprecursor was chain-extended into the silicone polyoxamide elastomerusing ethylenediamine following general procedure of Example 3 in U.S.Pat. No. 7,371,464 with the exception that only the precursor preparedabove was used instead a mixture of precursors and the reaction time wasfour days. The mole ratio of precursor to ethylenediamine was 1 to 1.The material was used neat without determining the hardness.

Examples 1-12. Solvent-based coatings were prepared from high molecularweight silicone gum. The components of Examples 1-12, shown in Table 2A,were dissolved in toluene at 25 weight % total solids to yieldhomogeneous solutions. These solutions were coated on a SCOTCHPAR PETfilm (51 micron polyethylene terephthalate film from 3M Company) using aknife coater. The toluene was removed by placing the coating in a dryingoven maintained at 70° C. for 10 minutes. The dry thickness of theadhesives in Examples 1-12 was 51 microns (2 mils). The samples werelaminated with the SILFLU M50 MD07 release liner (obtained fromSiliconature, Inc., Venice, Italy).

TABLE 2A Composition of Examples 1-12. Parts by weight EL Polymer SPOxDC-200-A TMS-803 EX. NA Elastomer PDMS fluid MQ tackifier 1 40 20 40 0 257.5 7.5 30 5 3 42.5 12.5 30 15 4 70 0 30 0 5 70 0 25 5 6 70 0 10 20 760 0 40 0 8 60 0 35 5 9 60 0 15 25 10 50 0 35 15 11 50 0 25 25 12 50 015 35

These samples were then irradiated with either electron beam radiationat an acceleration voltage of 220 keV, or gamma radiation as denoted inTable 2B. The peel adhesion and probe tack properties were measured andare also reported in Table 2B.

TABLE 2B Properties of cured samples of Examples 1-12. Dose Peel ForceProbe EX. Radiation (Mrad) (g/2.54 cm) Comments Tack (g) 1 E-Beam 2 10clean peel 119 2.5 8 clean peel 89 2 E-Beam 2 49 clean peel 128 2.5 24clean peel 91 3 E-Beam 2 85 clean peel 119 2.5 72 clean peel 115 4E-Beam 2 8 clean peel 126 2.5 7 clean peel 64 5 E-Beam 2 21 clean peel131 2.5 23 clean peel 129 6 E-Beam 2 73 clean peel 142 2.5 103 cleanpeel 104 7 E-Beam 2 8 clean peel 114 2.5 16 clean peel 86 8 E-Beam 2 31clean peel 192 2.5 101 clean peel 151 9 E-Beam 2 114 clean peel 143 2.566 clean peel 142 Gamma 0.2 — cohesive split — 2.5 11 clean peel 84 3 11clean peel 81 10 E-Beam 2 60 clean peel 180 2.5 91 clean peel 160 Gamma0.2 — cohesive split — 2.5 18 clean peel 87 3 14 clean peel 91 11 E-Beam2 91 clean peel 170 2.5 108 clean peel 190 Gamma 0.2 — cohesive split —2.5 15 clean peel 101 3 14 clean peel 88 12 E-Beam 2 94 clean peel 1652.5 168 clean peel 200 Gamma 0.2 — cohesive split — 2.5 24 clean peel142 3 54 clean peel 103

Examples 13-16. Solventless coatings were prepared from low molecularweight silicone oils or fluids, including a terminal silanol functionalPDMS. Although the coatings included a functional PDMS, they were nottypical of commercial reactive silicone systems. In particular, as thecoating did not contain any materials having functional groups reactivewith the terminal silanol groups, no chemical crosslinking would occurwith the systems of Examples 13-16.

The formulation components of Examples 13-16, shown in Table 3A, wereadded to a jar and allowed to mix for at least 48 hours to produce ahomogeneous solution. These solutions were coated on SCOTCHPAK PET filmusing a knife coater to yield 150 micron (6 mil) thick films. Thesesamples were irradiated with electron beam radiation using anacceleration voltage of 280 keV. The electron beam dose and the measuredpeel adhesion and probe tack properties are reported in Table 3B.

TABLE 3A Composition of Examples 13-16. Parts by weight DMS S42 DC-200-BTMS-803 EX. PDMS fluid PDMS fluid MQ tackifier 13 100 0 0 14 95 0 5 1545 50 5 16 28 67 5

TABLE 3B Properties of electron beam cured samples of Examples 13-16.Dose Peel Force Probe EX. Radiation (Mrad) (g/2.54 cm) Comments Tack (g)13 E-Beam 7 26 clean peel 118 8 6 clean peel 70 14 E-Beam 6 87 cleanpeel 194 7 60 clean peel 207 15 E-Beam 8 53 clean peel 173 9 33 cleanpeel 190 16 E-Beam 9 53 clean peel 164 10 18 clean peel 181

Examples 17-21. Solventless coatings were prepared from low molecularweight silicone oils or fluids. These coatings included onlynon-functional PDMS. The formulation components of Examples 17 through21, shown in Table 4A, were added to a jar and allowed to mix for atleast 48 hours to produce a homogeneous solution. These solutions werecoated on SCOTCHPAK PET film using a knife coater to yield 150 micron (6mil) thick films. These samples were irradiated with electron beamradiation using an acceleration voltage of 280 keV. The electron beamdose and the measured peel adhesion and probe tack properties arereported in Table 4B.

TABLE 4A Composition of Examples 17-21. Parts by weight DC-200-BDC-200-A (12,500 cSt (5000 cSt TMS-803 EX. PDMS fluid) PDMS fluid) MQtackifier 17 100 0 0 18 98 0 2 19 95 0 5 20 91 0 9 21 64 31 5

TABLE 4B Properties of cured samples of Examples 17-21. Dose Peel ForceProbe EX. Radiation (Mrad) (g/2.54 cm) Tack (g) 17 E-Beam 7 22 146 18E-Beam 7 40 207 19 E-Beam 7 48 191 20 E-Beam 7 58 199 21 E-Beam 7 47 174

Examples 22-24. The formulation components of Examples 22 through 24,shown in Table 5A, were added to a jar and allowed to mix for at least48 hours to produce a homogeneous solution.

TABLE 5A Composition of Examples 22-24. Parts by weight OHX-4070Terminal silanol Parts by wt. functional PDMS TMS-803 tackifer per 100EX. fluid (50,000 cSt)) MQ tackifier parts PDMS fluid 22 87 13 10 23 7723 15 24 69 31 20

These solutions were coated on a film consisting of apolyester/cellulose acetate woven fabric that has been heat laminated toa 25 micron (1 mil) Hytrel™ film. The coating was applied using a knifecoater to yield films of various thicknesses. These samples wereirradiated with electron beam radiation using an acceleration voltage of280 keV. The peel adhesions from a propylene panel and from human skinwere tested and the results are reported in Table 5B, along with theelectron beam dose. Due the high variability associated with testing onhuman skin, the standard deviation (std.) for the peel from skin is alsoreported.

TABLE 5B Properties of cured samples of Examples 22-24. E- 180 degreepeel adhesion (g/2.54 cm) Adhesive beam Human skin Human skin thicknessDose Polypropylene (T-0) (T-72) EX. Radiation (microns) (Mrad) panelAvg. std. Avg. std. 22 E-Beam 130 7 58 60 15 42 24 (5 mils) 180 7 65 6211 57 20 (7 mils) 23 E-Beam  75 8 50 60 7 52 15 (3 mils) 130 8 75 66 1254 21 (5 mils) 180 8 81 76 8 64 22 (7 mils) 24 E-Beam 130 8.5 79 83 1263 25 (5 mils) 180 8.5 102 96 21 66 33 (7 mils)

For comparison, the T-0 and T-72 180 degree peel adhesions to skin fortwo commercially available medical adhesive products were tested.MEPITAC soft silicone dressing tape (available from Molnlycke HealthCare) had a T-0 peel adhesion to human skin of 68 (+/−12) grams per 2.54cm, and a T-72 peel adhesion to human skin of 58 (+/−23) grams per 2.54cm. MICROPORE surgical tape (available from 3M Company) had a T-0 peeladhesion to human skin of 65 (+/−44) grams per 2.54 cm, and a T-72 peeladhesion to human skin of 145 (+/−46) grams per 2.54 cm.

In some embodiments, the silicone gel adhesives of the presentdisclosure are particularly suitable for adhesion to skin. Generally,the adhesives of the present disclosure have a lower surface tensionthan skin, therefore allowing the adhesive to wet quickly andextensively. The gel adhesive also spread under low deformation ratewhen enhanced by light pressure and have viscoelastic properties suchthat they deliver the desired level of adhesion in terms of intensityand duration.

The adhesives are cross-linked poly dimethylsiloxanes and theirproperties are mainly based on the ability of the surface to quickly wetthe substrate and conform to it without excessive flow. Only smalldissipation of energy occurs when deformation pressure is applied. Theadvantage of such adhesives is atraumatic removal, e.g., no skinstripping and no painful pulling of hair or skin. Another property isthat the adhesives have a low viscous component that limits their flowand the attachment of epithelial cells, hence it can be removed andadhered easily to the same or other skin surface.

Various modifications and alterations of this invention will becomeapparent to those skilled in the art without departing from the scopeand spirit of this invention.

1-15. (canceled)
 16. An adhesive comprising a radiation cured siliconegel, wherein the adhesive is prepared without a catalyst, wherein thesilicone gel comprises a crosslinked poly diorganosiloxane material anda noncrosslinked poly diorganosiloxane fluid.
 17. The adhesive of claim16, wherein the crosslinked poly diorganosiloxane material comprises acrosslinked poly dimethylsiloxane material and the noncrosslinked polydiorganosiloxane fluid comprises a noncrosslinked poly dimethylsiloxanefluid.
 18. The adhesive of claim 17, wherein the poly dimethylsiloxaneis selected from the group consisting of one or more silanol terminatedpoly dimethylsiloxanes, one or more non-functional polydimethylsiloxanes, and combinations thereof.
 19. The adhesive of claim17, wherein the poly dimethylsiloxane consists of one or morenon-functional poly dimethylsiloxanes.
 20. The adhesive of claim 16,wherein the adhesive further comprises a silicate resin tackifier. 21.The adhesive of claim 16, wherein the adhesive further comprises apoly(dimethylsiloxane-oxamide) linear copolymer. 22-23. (canceled) 24.The adhesive of claim 16, wherein the adhesive has a 180 degree peeladhesion from human skin of no greater than 200 grams per 2.54centimeters as measured according to the Skin Peel Adhesion Procedure.25. A medical article comprising a layer of the adhesive according toclaim 16 adhered to a medical substrate.
 26. The article of claim 25,wherein the layer has a thickness of 20 to 200 microns.
 27. An adhesiveformed by exposing a composition comprising a poly diorganosiloxanematerial to at least one of electron beam irradiation and gammairradiation at a sufficient dose to crosslink the poly diorganosiloxanematerial and form a radiation cured silicone gel, wherein the siliconegel comprises a crosslinked poly diorganosiloxane material and anoncrosslinked poly diorganosiloxane fluid, wherein the adhesive isprepared without a catalyst.
 28. The adhesive of claim 27, wherein thecrosslinked poly diorganosiloxane material comprises a crosslinked polydimethylsiloxane material and the noncrosslinked poly diorganosiloxanefluid comprises a noncrosslinked poly dimethylsiloxane fluid.
 29. Theadhesive of claim 28, wherein the poly dimethylsiloxane is selected fromthe group consisting of one or more silanol terminated polydimethylsiloxanes, one or more non-functional poly dimethylsiloxanes,and combinations thereof.
 30. The adhesive of claim 28, wherein the polydimethylsiloxane consists of one or more non-functional polydimethylsiloxanes.
 31. The adhesive of claim 27, wherein the adhesivefurther comprises a silicate resin tackifier.
 32. The adhesive of claim27, wherein the adhesive further comprises apoly(dimethylsiloxane-oxamide) linear copolymer.
 33. The adhesive ofclaim 16, wherein the adhesive further comprises a hydrophilic polymer.